WO2000066041A1

WO2000066041A1 - Intraocular lenses

Info

Publication number: WO2000066041A1
Application number: PCT/US2000/007698
Authority: WO
Inventors: Helene Lamielle; Laurent Hoffmann; Vincent Blanchard
Original assignee: Bausch & Lomb Surgical, Inc.
Priority date: 1999-04-29
Filing date: 2000-03-23
Publication date: 2000-11-09
Also published as: CA2370859A1; BR0011218A; HK1045248A1; EP1173114A1; US6200344B1; AU3912400A; AR029357A1; JP2002542885A; CA2370859C; AU775571B2; MXPA01010983A

Abstract

A refractive intraocular lens (32) including an optic portion (34) having an outer peripheral edge (36) and two opposed looped haptic elements (38). Each looped haptic element (38) is formed to have two broad connecting portions (40), two radial orientation portions (42), two spring portions (44) and a linking portion (46) for supporting the optic portion (34) in a patient's eye (10). The two broad connecting portions (40) of each looped haptic element (38) is permanently connected to the outer peripheral edge (36) of the optic portion (34). Each looped haptic element (38) is likewise formed to have greater resistance to bending in a plane generally parallel to an eye's optical axis than in a plane generally perpendicular to the eye's optical axis. The intraocular lens (32) is so designed to exhibit less than approximately 1.0 mm axial displacement or tilting of the optic portion (34) along the eye's optical axis under a compression force suitable to effect a 1.0 mm in diameter compression in overall length of the intraocular lens (32).

Description

INTRAOCULAR LENSES

FIELD OF THE INVENTION

The present invention relates to intraocular lenses (lOLs) and a

method for making and using the same. More particularly, the present

invention relates to lOLs designed primarily for refractive correction in aphakic

eyes. lOLs made in accordance with the present invention are used in

aphakic eyes to replace a surgically removed diseased natural lens, such as

in the case of cataracts.

BACKGROUND OF THE INVENTION

IOL implants have been used for years in aphakic eyes as

replacements for diseased natural crystalline lenses that have been surgically

removed from the eyes. Many different IOL designs have been developed

over past years and proven successful for use in aphakic eyes. The

successful IOL designs to date primarily include an optic portion with supports

therefor, called haptics, connected to and surrounding at least part of the

optic portion. The haptic portions of an IOL are designed to support the optic

portion of the IOL in the lens capsule, anterior chamber or posterior chamber

of an eye. Commercially successful lOLs have been made from a variety of

biocompatible materials, ranging from more rigid materials such as

polymethylmethacrylate (PMMA) to softer, more flexible materials capable of

being folded or compressed such as silicones, certain acrylics, and hydrogels.

Haptic portions of the lOLs have been formed separately from the optic

portion and later connected thereto through processes such as heat, physical

staking and/or chemical bonding. Haptics have also been formed as an

integral part of the optic portion in what is commonly referred to as "single-

piece" lOLs.

Softer, more flexible lOLs have gained in popularity in more recent

years due to their ability to be compressed, folded, rolled or otherwise

deformed. Such softer lOLs may be deformed prior to insertion thereof

through an incision in the cornea of an eye. Following insertion of the IOL in

an eye, the IOL returns to its original pre-deformed shape due to the memory

characteristics of the soft material. Softer, more flexible lOLs as just

described may be implanted into an eye through an incision that is much

smaller, i.e., 2.8 to 3.2 mm, than that necessary for more rigid lOLs, i.e., 4.8

to 6.0 mm. A larger incision is necessary for more rigid lOLs because the

lens must be inserted through an incision in the cornea slightly larger than the

diameter of the inflexible IOL optic portion. Accordingly, more rigid lOLs have

become less popular in the market since larger incisions have been found to be associated with an increased incidence of postoperative complications,

such as induced astigmatism.

After IOL implantation, both softer and more rigid lOLs are subject to

compressive forces exerted on the outer edges thereof, which typically occur

when an individual squints or rubs the eye. These compressive forces may

result in decentration of the IOL and distortion of the visual image.

Compressive forces exerted on an IOL also tend to cause the lens to tilt or

have axial displacement of the IOL along the optical axis of an eye.

Movement of an IOL along the optical axis of an eye has the potential to

cause the IOL to contact and damage delicate eye tissues. Also, lOLs of

current designs, whether formed of either softer or more rigid materials, tend

to deflect along the optical axis of an eye when the haptics are compressed.

IOL manufacturers provide a wide range of IOL sizes to more precisely fit

lOLs to each particular patient's eye size. Providing a wide range of IOL

sizes is an attempt to minimize the potential for axial displacement of the IOL

along the optical axis of an eye.

Because of the noted shortcomings of current IOL designs, there is a

need for lOLs designed to minimize tilt or axial displacement of the IOL optic

portion along the optical axis of the eye when compressive forces are exerted

against the outer edges thereof. By lessening an lOL's movement along the

optical axis of an eye, more certain refractive correction may be achieved and

the risk of tissue damage may be reduced. SUMMARY OF THE INVENTION

An intraocular lens (IOL) made in accordance with the present

invention has an optic portion with an outer peripheral edge and two looped

haptic elements for supporting the optic portion in a patient's eye. The

subject IOL is balanced having one looped haptic element formed on one

edge of the optic and the other looped haptic element formed on an opposed

edge of the optic. Each of the looped haptic elements has two broad

connecting portions, two radial orientation portions, two spring portions and a

linking portion connecting the two spring portions. The two broad connecting

portions of each looped haptic element are connected to the outer peripheral

edge of the optic portion. Each looped haptic element forms a large

fenestration to enhance capsular fixation once within an eye. The looped

haptic elements' spring portions and linking portions are designed to engage

an inner surface of a patient's eye.

Each looped haptic element's broad connecting portions are designed

to achieve optimal optic stability by avoiding tilt and axial displacement.

Within these broad connecting portions, each looped haptic element is

designed to bend in a plane generally perpendicular to the optical axis of an

eye rather than in a plane generally parallel to the optical axis of an eye. By

providing looped haptic elements with this type of flexibility characteristic, the

present IOL tends to have maximized stability within an eye. The flexibility characteristic of the subject looped haptic elements relative to the optic

portion eliminates unacceptable tilting or axial displacement of the optic

portion along the optical axis when compressive forces are exerted against

the looped haptic elements of the IOL.

Accordingly, it is an object of the present invention to provide

intraocular lenses for use in aphakic eyes.

Another object of the present invention is to provide intraocular lenses

for use in aphakic eyes with flexibility characteristics which maximize stability

thereof.

Another object of the present invention is to provide intraocular lenses

for use in aphakic eyes, which minimize tilt or axial displacement of the optic

portions of the lenses along the optical axis of the eyes.

Another object of the present invention is to provide intraocular lenses

for use in aphakic eyes, which minimize damage to tissues in the interior of

the eyes.

Still another object of the present invention is to provide intraocular

lenses, which are resistant to decentration within the eyes.

These and other objectives and advantages of the present invention,

some of which are specifically described and others that are not, will become

apparent from the detailed description, drawings and claims that follow,

wherein like features are designated by like numerals. BRIEF DESCRIPTION OF THE DRAWINGS

FIGURE 1 is a schematic representation of the interior of a human eye

including a natural lens;

FIGURE 2 is a plan view of an IOL with an optic and two looped haptic

elements made in accordance with the present invention;

FIGURE 3 is a side view of the IOL of Figure 2;

FIGURE 4 is a side view of the IOL of Figure 2 with sharper peripheral

edges on a posterior surface of the optic;

FIGURE 5 is a side view of the IOL of Figure 2 with sharper edges on

the two looped haptic elements;

FIGURE 6 is a side view of the IOL of Figure 2 with rounder edges on

the two looped haptic elements; and

FIGURE 7 is a side view of a looped haptic element of Figure 2 taken

along line 7-7 with a stiffening element therein.

DETAILED DESCRIPTION OF THE INVENTION

Figure 1 illustrates a simplified diagram of an eye 10 showing landmark

structures relevant to the implantation of an intraocular lens of the present

invention. Eye 10 includes an optically clear cornea 12 and an iris 14. A

natural crystalline lens 16 and a retina 18 are located behind the iris 14 of eye

10. Eye 10 also includes anterior chamber 20 located in front of iris 14 and

posterior chamber 22 located between iris 14 and natural lens 16. lOLs of the present invention are preferably implanted into lens capsule 24 or

posterior chamber 22 to refract light after a diseased natural lens 16 has been

surgically removed (aphakic application). Eye 10 also includes an optical

axis OA-OA that is an imaginary line that passes through the optical center 26

of anterior surface 28 and posterior surface 30 of lens 16. Optical axis OA-

OA in the human eye 10 is generally perpendicular to a portion of cornea 12,

natural lens 16 and retina 18.

The IOL of the present invention, as best illustrated in Figures 2 and 3,

is identified by reference numeral 32. IOL 32 is designed for implantation

preferably in lens capsule 24 or posterior chamber 22 of a patient's aphakic

eye 10. IOL 32 has an optic portion 34 with an outer peripheral edge 36.

Preferably integrally formed on peripheral edge 36 of optic portion 34 are two

opposed looped haptic elements 38, each having two broad connecting

portions 40, two radial orientation portions 42, two spring portions 44 and a

linking portion 46. Broad connecting portions 40 are preferably integrally

formed with and permanently connected to outer peripheral edge 36 of optic

portion 34. Alternatively however, looped haptic elements 38 may be

attached to optic portion 34 by staking, chemical polymerization or other

methods known to those skilled in the art.

In accordance with the present invention, each looped haptic element

38 is designed to preferably engage inner surfaces 48 in lens capsule 24 or

surfaces 50 in posterior chamber 22. Looped haptic elements 38 are designed so that when IOL 32 is implanted in a patient's eye 10 and held in

place through compressive forces exerted by inner surfaces 48 or 50, looped

haptic elements 38 flex to accommodate the particular size of eye 10.

Looped haptic elements 38 are designed to be resistent to flexing and tilting

in a plane generally parallel to that of optical axis OA-OA of eye 10. By

designing this type of flexibility characteristic into looped haptic elements 38,

IOL 32 may be manufactured in one or a few standard sizes and be a suitable

fit for most sizes of patients' eyes 10. The flexibility characteristic of looped

haptic elements 38 also minimize axial displacement of optic portion 34 in a

direction along optical axis OA-OA of eye 10.

Broad connecting portions 40 of looped haptic elements 38 attach the

looped haptic elements 38 to optic portion 34 of IOL 32. The broad

connecting portions 40 are designed to be broad to increase rigidity and to

minimize axial displacement or tilting of IOL 32. Broad connecting portions 40

likewise prevent the snagging or catching of eye 10 structures such as the

rhexis 52 on optic 34. Each broad connecting portion 40 preferably measures

to equal 10 to 20 percent of the circumference of the optic portion 34.

Radial orientation portions 42 of looped haptic elements 38 have

interior surfaces 54 and exterior surfaces 56. Interior surfaces 54 and exterior

surfaces 56 are formed with an outward curve to increase the stability of IOL

32 when implanted in eye 10. Outer ends 58 of radial orientation portions 42

are of a significantly smaller width than that of radial orientation portions 42 at broad connecting portions 40 to minimize the surface area thereof. The

surface area of outer ends 58 is designed to be as small as possible to

minimize the lOL's 32 contact with the lens capsule's 24 equatorial

germination zone 60 thereby decreasing cellular growth and posterior

capsular opacification of IOL 32. The width of outer ends 58 is also designed

to be smaller than that of the thickness of looped haptic elements 38 to allow

for flexing of spring portions 44 in a plane perpendicular to optical axis OA-OA

of eye 10.

Spring portions 44 have an interior surface 62 and an exterior surface

64. Spring portions 44 are designed to absorb compressive forces exerted by

the eye 10 and maintain IOL alignment within lens capsule 24. Spring

portions 44 when compressed upon absorption of compressive forces deform

whereby interior surfaces 62 may abut outer ends 58. Also, when placed

under sufficient compressive forces, each spring portion 44 may deflect

outwardly in a direction away from its adjacent spring portion 44 and

downwardly in a direction toward optic portion 34 to absorb such forces and

avoid undesirable flexing and tilting in a plane parallel to the optical axix OA-

OA of eye 10.

Linking portions 46 connect adjacent spring portions 44 to form a

looped haptic element 38. Linking portions 46 are slightly bowed at

preferably less than 20 degrees but more preferably at less than 10 degrees

but greater than 1 degree inwardly toward optic portion 34 to form depressions 66. Upon one or more spring portions 44 being deflected

outwardly in a direction away from its adjacent spring portion 44 and

downwardly in a direction of optic portion 34 when placed under compressive

forces, depression(s) 66 of linking portion(s) 46 looses its bow and becomes

more linear.

Fenestration 68 defined by interior surfaces 54 and 62, and interior

surfaces 70 of linking portion 46 enhances fixation of IOL 32 within lens

capsule 24 or posterior chamber 22.

Compressive forces of differing magnitudes within the range of

approximately 2 to 8 mN exerted against looped haptic elements 38 effecting

an approximately 2.0 mm in overall length compression of IOL 32, such as

that caused by differing eye sizes or compressive forces by the eye 10,

results in less than approximately 1.0 mm, but more preferably less than

approximately 0.5mm and most preferably less than approximately 0.3 mm

axial displacement or tilting of optic portion 34 along optical axis OA-OA in an

eye 10. Under like compressive forces, lOLs known in the art result in

approximately 2.0 mm axial displacement of the optic portion along the optical

axis in the eye, which may damage delicate tissues therein. The unique

design of IOL 32 achieves significantly minimized axial displacement or tilting

of optic portion 34 to protect the eye 10 from damage when compressive

forces are applied to eye 10. The flexibility characteristic of looped haptic elements 38 of IOL 32 as

described above is achieved through the unique design thereof. The exterior

surface 72 of linking portion 46 and the exterior surface 64 of spring portions

44 may be formed with either rounded edges 74 depicted in Figure 6 for a

smoother fit with inner surfaces 48 or 50, or more defined, sharper edges 76

depicted in Figure 5 to provide a barrier to prevent cellular migration and

growth. Another feature which may be incorporated into the subject lens is a

sharper peripheral edge 36 on posterior surface 35 of optic portion 34 as

depicted in Figure 4 to provide a barrier to prevent cellular migration and

growth.

The subject IOL 32 is preferably produced having an optic portion 34

approximately 4.5 to 9.0 mm, but preferably approximately 5.0 to 6.5 mm and

most preferably 5.5 mm in diameter and approximately 0.5 mm to 1.0 mm, but

preferably approximately 0.6 to 0.8 mm and most preferably 0.7 mm in

thickness at peripheral edge 36. Looped haptic elements 38 increase or

decrease in overall length depending upon the diameter of optic portion 34 so

that the overall length of IOL 32 remains generally consistent. As the

diameter of optic portion 34 increases, the overall length of looped haptic

elements 38 decrease. Likewise, as the diameter of optic portion 34

decreases, the overall length of looped haptic elements 38 increase. In

general, looped haptic elements 38 are formed to be approximately 8.5 to

13.5 mm, but preferably approximately 9.0 to 12.0 mm and most preferably approximately 10.5 mm in overall length. Such overall length is obtained

measuring from the center of broad connecting portion 40 around through the

center of looped haptic element 38 to the center of adjacent broad connecting

portion 40. The width of looped haptic elements 38 measuring the distance

between the outer tips 80 of spring portions 44 is approximately 4.5 to 9.0

mm, but preferably approximately 5.0 to 6.5 mm and most preferably 5.5 mm.

Looped haptic elements 38 have the same thickness thoughout their entire

length which is approximately 0.2 to 0.9 mm, but preferably approximately 0.3

to 0.7 mm and most preferably approximately 0.55 mm. Spring portions 44

measuring the distance from outer end 58 to exterior surface 64 at linking

portion 46 are approximately 0.4 to 1.5 mm, but preferably approximately 0.6

to 1.2 mm and most preferably approximately 0.8 mm. Radial orientation

portions 42 are approximately 1.6 to 4.5 mm, but preferably approximately 2.0

to 4.0 mm and most preferably approximately 3.0 mm in length measuring

from the center of broad connecting portion 40 to the center of outer end 58.

The desired flexibility characteristic of looped haptic elements 38 of

IOL 32 may likewise be achieved or enhanced by incorporating a stiffening

element 82, in the shape of a ribbon, in looped haptic elements 38, as

illustrated in Figure 7. Stiffening elements 82 may be positioned in looped

haptic elements 38 to function in a manner similar to that of an I-beam in

construction to prevent axial displacement or tilting along optical axis OA-OA

when compressive force is applied to looped haptic elements 38. Stiffening elements 82 are formed of a less flexible material than that

of IOL 32. Suitable materials for stiffening elements 82 include but are not

limited to polyimides, polyolefins, high-density polyethylenes, polyesters,

nylons, metals or any biocompatible material with suitable stiffening

characteristics. Stiffening elements 82 may be used in conjunction with

looped haptic elements 38 as described above or in cases where a thinner

looped haptic design is desired while still achieving the desired flexibility

characteristics.

Suitable materials for the production of the subject IOL 32 include but

are not limited to foldable or compressible materials, such as silicone

polymers, hydrocarbon and fluorocarbon polymers, hydrogels, soft acrylic

polymers, polyesters, polyamides, polyurethane, silicone polymers with

hydrophilic monomer units, fluorine-containing polysiloxane elastomers and

combinations thereof. The preferred material for the production of IOL 32 of

the present invention is a hydrogel made from 2-hydroxyethyl methacrylate

(HEMA) and 6-hydroxyhexyl methacrylate (HOHEXMA), i.e., poly(HEMA-co-

HOHEXMA). Poly(HEMA-co-HOHEXMA) is the preferred material for the

manufacture of IOL 32 due to its equilibrium water content of approximately

18 percent by weight, and high refractive index of approximately 1.474, which

is greater than that of the aqueous humor of the eye, i.e., 1.33. A high

refractive index is a desirable feature in the production of lOLs to impart high

optical power with a minimum of optic thickness. By using a material with a high refractive index, visual acuity deficiencies may be corrected using a

thinner IOL. Poly(HEMA-co-HOHEXMA) is also a desirable material in the

production of lOLs 32 due to its mechanical strength, which is suitable to

withstand considerable physical manipulation. Poly(HEMA-co-HOHEXMA)

also has desirable memory properties suitable for IOL use. lOLs

manufactured from a material possessing good memory properties such as

those of poly(HEMA-co-HOHEXMA) unfold in a controlled manner in an eye,

rather than explosively, to its predetermined shape. Explosive unfolding of

lOLs is undesirable due to potential damage to delicate tissues within the eye.

Poly(HEMA-co-HOHEXMA) also has dimensional stability in the eye.

Although the teachings of the present invention are preferably applied

to soft or foldable lOLs formed of a foldable or compressible material, the

same may also be applied to harder, less flexible lenses formed of a relatively

rigid material such as polymethyl methacrylate (PMMA) having flexible haptics

formed either of the same or a different material.

Optic portion 34 of IOL 32 can be a positive powered lens from 0 to

approximately +40 diopters or a negative powered lens from 0 to

approximately -30 diopters. Optic portion 34 may be biconvex, plano¬

convex, plano-concave, biconcave or concave-convex (meniscus), depending

upon the power required to achieve the appropriate central and peripheral

thickness for efficient handling. Optic portion 34 of the subject IOL 32 may optionally be formed with a

glare reduction zone 84 of approximately 0.25 to 0.75 mm but more

preferably approximately 0.3 to 0.6 mm and most preferably 0.5 mm in width

adjacent outer peripheral edge 36 for reducing glare when outer peripheral

edge 36 of IOL 32 is struck by light entering eye10 during high light or at

other times when pupil 86 is dilated. Glare reduction zone 84 is typically

fabricated of the same material as optic portion 34, but may be opaque,

colored or patterned in a conventional manner to block or diffuse light in plane

with optical axis OA-OA.

Subject IOL 32 is preferably manufactured by first producing discs from

a material of choice as described in U.S. Patent Nos. 5,217,491 and

5,326,506 each incorporated herein in its entirety by reference. IOL 32 may

then be machined from the material discs in a conventional manner. Once

machined, IOL 32 may be polished, cleaned, sterilized and packaged by a

conventional method known to those skilled in the art.

Subject IOL 32 is used in eye 10 by creating an incision in cornea 12,

inserting IOL 32 in posterior chamber 22 and closing the incision.

Alternatively, IOL 32 may be used in eye 10 by creating an incision in cornea

12 and lens capsule 24, removing natural lens 16, inserting IOL 32 in lens

capsule 24 and closing the incision.

IOL 32 of the present invention provides for a refractive lens suitable

for use in lens capsule 24 or posterior chamber 22. IOL 32 has looped haptic elements 38 with flexibility characteristics that minimize axial displacement or

tilting along optical axis OA-OA of eye 10 thereby preventing decentration of

IOL 32, distortion of vision and damage to delicate tissues within eye 10. IOL

32, having the flexibility characteristics described herein is also advantageous

because one or a few lens sizes suitably fit eyes 10 of most sizes. By

providing a "universal" lens such as that of the present invention, clinical risks

to patients due to improperly sized lenses are minimized. Such clinical risks

minimized include pupil ovalization, corneal endothelium damage and poor

fixation. Likewise, manufacturers' need to produce lOLs of many sizes to fit

eyes of many sizes is eliminated, thus reducing production and inventory

costs associated therewith. Ophthalmologists also benefit from subject IOL

32 in that time is saved by eliminating the need to determine each patient's

eye size and costs associated with maintaining large inventories of varying

sized lenses.

While there is shown and described herein certain specific

embodiments of the present invention, it will be manifest to those skilled in the

art that various modifications may be made without departing from the spirit

and scope of the underlying inventive concept and that the same is not limited

to the particular forms herein shown and described except insofar as

indicated by the scope of the appended claims.

Claims

We claim:

1. An intraocular lens to be implanted within an eye generally

perpendicular to the eye's optical axis comprising:

an outer peripheral edge defining an optic portion, and

two looped haptic elements permanently connected to the outer

peripheral edge,

whereby a compressive force sufficient to effect a 1.0 mm in

diameter compression of said lens results in less than

approximately 1.0 mm of axial displacement of said optic portion

along the eye's optical axis.

2. An intraocular lens to be implanted within an eye generally

perpendicular to the eye's optical axis comprising:

an outer peripheral edge defining an optic portion, and

two looped haptic elements permanently connected to the outer

peripheral edge,

whereby a compressive force sufficient to effect a 1.0 mm in

diameter compression of said lens results in less than

approximately 0.5 mm of axial displacement of said optic portion

along the eye's optical axis.

3. An intraocular lens to be implanted within an eye generally

perpendicular to the eye's optical axis comprising:

an outer peripheral edge defining an optic portion, and

two looped haptic elements permanently connected to the outer

peripheral edge,

whereby a compressive force sufficient to effect a 1.0 mm in

diameter compression of said lens results in less than

approximately 0.3 mm of axial displacement of said optic portion

along the eye's optical axis.

4. The intraocular lens of claim 1 , 2 or 3 wherein the looped

haptic elements and the optic portion are both formed of a foldable

or compressible material.

5. The intraocular lens of claim 1 , 2 or 3 wherein said lens is

formed from a material selected from the group consisting of

silicone polymers, hydrocarbon and fluorocarbon polymers,

hydrogels, soft acrylic polymers, polyester, polyamides,

polyurethane, silicone polymers with hydrophilic monomer units, fluorine-containing polysiloxane elastomers and combinations

thereof.

6. The intraocular lens of claim 1 , 2 or 3 wherein said lens is

formed from a hydrogel material.

7. The intraocular lens of claim 1 , 2 or 3 wherein said lens is

formed from a hydrogel material which is 18 percent by weight

water.

8. The intraocular lens of claim 1 , 2 or 3 wherein said lens is

formed from poly(HEMA-co-HOHEXMA).

9. The intraocular lens of claim 1 , 2 or 3 wherein said lens is

formed from a material having a refractive index above 1.33.

10. The intraocular lens of claim 1 , 2 or 3 wherein said lens is

formed from an acrylic material.

11. The intraocular lens of claim 1 , 2 or 3 wherein said lens is

formed from a silicone material.

12. The intraocular lens of claim 1 , 2 or 3 wherein said looped

haptic elements are dimensioned to have a greater thickness in a

plane generally perpendicular to the eye's optical axis than in a

plane generally parallel to the eye's optical axis.

13. The intraocular lens of claim 1 , 2 or 3 wherein a glare

reduction zone is formed adjacent to the outer peripheral edge of

the optic portion.

14. The intraocular lens of claim 1 , 2 or 3 wherein said looped

haptic elements include a stiffening element having a greater

resistance to bending in a plane generally parallel to an eye's

optical axis than in a plane generally perpendicular to the eye's

optical axis.

15. The intraocular lens of claim 1 , 2 or 3 wherein the looped

haptic element includes a stiffening element formed from a material

selected from the group consisting of polyimide, polyolefin, high-

density polyester, nylon and metal.

16. A method of manufacturing the intraocular lens of claim 1 , 2

or 3 comprising: forming a disk of a suitable material, and

machining said lens from said disk.

17. A method of using the intraocular lens of claim 1 , 2 or 3

comprising:

creating an incision in a cornea of an eye, and

inserting said intraocular lens in a posterior chamber of said

eye.

18. A method of using the intraocular lens of claim 1 ,2 or 3

comprising :

creating an incision in a cornea and lens capsule of an eye,

removing a natural lens of said eye, and

inserting said intraocular lens in said lens capsule of said eye.